BIOMOLECULE MEASURING DEVICE
Provided is a biomolecule measuring device capable of effectively reducing measurement noise occurring when measuring a biomolecule sample using a semiconductor sensor. This biomolecule measuring device generates a trigger to react a sample with a reagent after starting to send the reagent onto the semiconductor sensor that detects ion concentration (see FIG. 7).
The present invention relates to a biomolecule measuring device.
BACKGROUND ARTIn recent years, biomolecule measuring devices using semiconductor technologies are drawing attentions. Patent Literature 1 listed below describes a DNA sequencer that cost-effectively and rapidly determines base sequences of deoxyribo nucleic acid (DNA) using pH sensor arrays manufactured with semiconductor technologies. Semiconductor sensors quantify reactions of target biomaterials according to magnitude of electrical signals. Therefore, semiconductor sensors do not require conventional expensive fluorescent reagents and thus are advantageous in terms of costs. It is possible to integrate millions to more than a billion sensors using semiconductor micro-processing technologies. It is also possible to activate each of such sensors in parallel to perform measurements. Therefore, the throughput of the measurement may be readily improved.
Ion Sensitive Field Effect Transistor (ISFET) is one of semiconductor sensors that is frequently used in the field of biomolecule measuring device. Details of ISFET will be described later. ISFET is a device that measures interface potentials induced on ion sensitive layers. Therefore, if there exists electric charges other than those derived from ions to be measured, measuring errors may be caused by such electric charges. However, plasma processing or ion injection are performed during manufacturing the device in semiconductor processes, thus it is likely that electric charges are accumulated in the device. Regarding that technical problem, Non Patent Literature 1 listed below describes that electric charges are accumulated especially at ion sensitive layers, protection layers, interfaces of electrodes, floating electrodes, or gate oxides. Non Patent Literature 2 listed below describes that such accumulation of electric charges may offset threshold voltages of ISFET by around ±10V.
It is known that ISFET has a technical problem referred to as drift in which characteristics shift during measurement process. Drift is a phenomenon caused by chemical reactions between ion sensitive layers and reagents during measurement process which causes the ion sensitive layer to trap electric charges. The amount of drift significantly depends on manufacturing process of the device or device structures. Non Patent Literature 3 listed below describes that the threshold voltage of transistor shifts at a rate of approximately 10 mV/hour.
The offset or drift of threshold voltage due to trapped charges may cause measuring errors and thus it is necessary to reduce them. Patent Literature 1 listed below describes, as a conventional technique for removing trapped charges, a method to irradiate ultraviolet ray to provide electric charge with energy, thereby withdrawing the charge from the device. Non Patent Literature 4 listed below describes that it is necessary to irradiate ultraviolet ray for long hours, e.g. for 10 hours. Non Patent Literature 1 describes that hot electron injection may reduce variations in threshold voltages due to trapped charges.
Another technical problem in utilizing ISFET for measuring biomolecules is that ISFET also outputs signals in response to variation in ion concentration when replacing reagent solutions. In other words, a signal due to replacing reagent solutions (i.e. background signal) is overlapped with the signal due to variation in ion concentration to be measured. For example, ISFET using Ta2O5 as ion sensitive layer is excellent in hydrogen ion selectivity and sensitivity, and is widely used as the pH sensor array in Patent Literature 1 and the like. However, Non Patent Literature 5 describes that such ISFET also outputs signals in response to potassium chloride ion in the solution.
In order to acquire only the target signal from the signal overlapped with background signals, it is necessary to estimate the background signal and to subtract the estimated background signal from the acquired signal. Patent Literature 2 listed below describes a method for estimating background signals using calculated signal value of ISFET in a reaction well not including biomolecules. When performing parallel measurement using one million to more than one million ISFETs as in the above-described semiconductor DNA sequencer, it is necessary to perform the above-described background processing for all of measured data in all reaction wells. Then the background processing increases the analyzing time. This indicates that the time until the measurement result is acquired is elongated. Therefore, the background processing time should be reduced as far as possible.
CITATION LIST Patent Literature
- Patent Literature 1: JP Patent Publication (Kohyo) 2010-513869 A
- Patent Literature 2: US Patent Publication 2012/0172241
- Non Patent Literature 1: Georgiou, et. al, Electronics Lett. October 2009
- Non Patent Literature 2: Liu, et. al, IEEE Trans. Elec. Dev, December, 2011
- Non Patent Literature 3: Hammond, et. al, IEEE Sensors, December 2004
- Non Patent Literature 4: Milgrew, et. Al, IEEE Elec. Dev., April 2008
- Non Patent Literature 5: Kerkhof, et. al, Sensors and Actuators B, 1994
The methods for removing trapped charges by irradiating ultraviolet rays described in Patent Literature 1 and Non Patent Literature 4 require irradiating the ultraviolet ray for long time, as mentioned above. This causes a technical problem of increased measuring time. Regarding method for reducing influences from trapped charges, Non Patent Literature 1 discusses about injecting hot electrons to a single ISFET. However, no method is discussed preferable for biomolecule measuring devices in which a plurality of ISFETs is arranged in arrayed manner. In addition, hot electron injection only works for increasing the threshold voltage.
It is conceivable that calibrating the characteristics of the device may be used as another solution. For example, in case of a pH sensor using a single ISFET, a calibration may be done using a standard solution as a pH reference, and then a correction may be applied outside the sensor, thereby keeping the measurement accuracy. However, in case of semiconductor sensor array in which a lot of ISFETs is allocated in arrayed manner, it is necessary to calibrate for each data from vast amount of ISFETs, which is impractical.
On the other hand, in the method regarding background processing described in Patent Literature 2, it is necessary to perform huge amount of calculations for estimating backgrounds and for calculating differences. Thus a lot of time is required from the beginning of measurement until acquiring the result. In addition, when estimating backgrounds using such as averaging calculations, the measurement accuracy for each ISFET may be decreased. Further, in order to precisely estimate backgrounds across wide value range, huge amount of data is required.
The present invention is made in the light of the above-mentioned technical problem. It is an objective of the present invention to provide a biomolecule measuring device that is capable of effectively reducing measurement noises occurring when measuring biomolecule samples using semiconductor sensors.
Solution to ProblemA biomolecule measuring device according to the present invention generates, after starting transmission of a reagent onto a semiconductor sensor that detects an ion concentration, a trigger to react the reagent with a sample.
Advantageous Effects of InventionWith the biomolecule measuring device according to the present invention, it is possible to effectively reduce measurement noises occurring when measuring biomolecule samples using semiconductor sensors that detect ion concentrations.
Technical problems, configurations, and advantageous effects other than those mentioned above will be apparent from the detailed descriptions of embodiments below.
Hereinafter, for the sake of promoting understanding of the present invention, a technical problem due to drift, offset, and background in conventional biomolecule measuring devices will be described first. Then embodiments of the present invention will be described.
<Technical Problem in Conventional Techniques: Regarding Measurement Error>In order to reduce influences from variations in characteristics of the ISFET 114, Patent Literature 2 estimates the background signal by averaging the measured waveform acquired from a plurality of the empty wells 112 around the well 111. However, the well 111 itself also has variations in characteristics. Therefore, even if the measured waveform acquired from a plurality of the empty well 112 is averaged, there still remains an error due to each of the wells 111. In addition, the processing load for estimation will be increased.
<Technical Problem in Conventional Techniques: Regarding Data Amount>As shown in
In order to remove the offset and the background from the waveform actually outputted from ISFET using computational process to finally acquire the signal waveform 201, it is necessary to record wide range of waveforms as shown in
For example, a theoretical voltage variation due to variation in hydrogen ion concentration may be calculated using Nernst equation. It is approximately 59 mV/pH at 25 degrees centigrade. Actual ISFET has a slightly lower value, i.e. tens of mV per pH. When measuring this voltage variation with precision of 1 mV, 14 to 15 bits of A/D conversion precision is required for recording all of waveform data offsetting by ±10V. Waveform variation due to pH variation ranges across several seconds. Therefore, when measuring at sampling rate of 100 Hz for 5 seconds, one unit of the ISFET 114 outputs approximately 1 Kbytes of data at each measurement. Assuming that the measurement is repeated 100 times and there are one million wells, the finally outputted data reaches 100 Gbytes. Thus huge amount of data must be stored for saving a plurality of measurement data. On the other hand, assuming that a signal derived from incorporation event varies between pH1-pH14, the voltage variation is 59 mV×14=826 mV, i.e. merely about 1V. Accordingly, even when measuring with precision of 1 mV, the A/D converter only requires 10 bits. Thus the amount of data will be reduced by approximately 30%.
As discussed above, considering the data amount, it is preferable to previously reduce drift, offset, and background of ISFET on the device before data processing. Alternatively, it is preferable if they can be removed only by simple calculations.
Embodiment 1Hereinafter, embodiments of the present invention will be described using figures. An example will be described where ISFET is used as the semiconductor sensor and where the biomolecule measuring device is configured as a DNA sequencer that determines DNA sequences. However, application of the present invention is not limited to DNA sequencers. The present invention may be widely applied to systems that electrically measure reactive products of biomolecules. Since ISFET can detect various types of ions by appropriately selecting the ion sensitive layer, the present invention may be applied to devices that measure biomolecules in which sodium ions or potassium ions vary, for example. In all figures describing the embodiments, same reference signs are basically assigned to same components, and repetitive explanations will be omitted.
Now returning back to
The ISFET 114 generally includes the ion sensitive layer 100, the protection layer 101, the floating gate 102, a gate electrode 103, the gate oxide 104, a drain 105, a source 106, a Si substrate 107, and a substrate contact 110. Some configurations do not include the floating gate 102 and the gate electrode 103, and the protection layer 101 and the ion sensitive layer 100 are stacked directly on the gate oxide 104. The ISFET 114 and the well 703 formed immediately above the ISFET 114 may be collectively referred to as a cell 116.
When measuring ions generated from the biomolecule 115, the sensitive layer 100 is contacted with the reagent solution 108 and the reference electrode 109 is immersed into the reagent solution 108. By applying a voltage VREF to the reference electrode 109 under this situation, a channel is induced between the drain 105 and the source 106 via capacitive coupling between the ion sensitive layer 100, the protection layer 101, and the gate oxide 104. Thus a drain current-reference electrode voltage characteristic is acquired depending on the characteristic of the ISFET 114.
The controller 312 performs, according to preprogrammed experiment sequences and to the data acquired by the data processor 311, processes of: adjusting the timing for transmitting solutions by the solution sending pumps of the solution sender 303 and adjusting the amount of transmitted solutions; controlling operational states of the ISFET array chip 1002; controlling the data processor 311; controlling voltages of the reference electrodes installed on any one of the reagent routes 302, 313, and 314 or installed on the ISFET chip 1002. The controller 312 also controls, according to the measured value by the temperature sensor 307 installed on the ISFET array chip 1002, the cooler 300 that cools the reagent solution and the heater 308 installed on the ISFET array chip 1002.
The data processor 311 acquires data indicating the measured result outputted from the ISFET array chip 1002 and analyzes the acquired data. The data processor 311 may be implemented by an interface board equipped with typical A/D converters and by a computer. The selector circuit 305 and the reading circuit 309 will be described later.
A method for determining the DNA sequence by detecting the hydrogen ion 408 may be defined as below. Firstly, the primer 406 is coupled with the unknown single-stranded DNA 405 which DNA sequence is to be determined. In this state, four types of reagents of dCTP, dTTP, dATP, and dGTP are sequentially injected. The hydrogen ion concentration is measured at each of the reagent injections. For example, if the hydrogen ion is generated when injecting dATP, the end portion of the single-stranded DNA excluding the portion coupled with the primer 406 is a complementary base of A, i.e. T. It is possible to sequentially determine the DNA sequence by repeating the process of reagent injection and of measuring hydrogen ion concentration.
The bead 702 is filled into the cell, and then the ISFET array chip 1002 is mounted on the device. The reagent dNTPs and the wash used for the reaction are previously cooled well below the optimum temperature of DNA polymerase using the cooler 300. After initiation of the measurement, the controller 312 selects a reagent dNTP according to the predefined sequence (S600). The solution sender 303 injects the reagent solution 108 into the cell on the ISFET array chip 1002 (S601). At this stage, the temperature of dNTP is low and DNA polymerase does not work almost at all. Thus the incorporation event hardly occurs.
(FIG. 7: Steps S602-S604)The controller 312 heats, as a trigger for inducing the incorporation event, the well 703 and the reagent solution 108 in the well 703 using the heater 308 on the chip, thereby activating DNA polymerase (S602). The ISFET 114 measures the incorporation signal induced by the heater 308 (S603). After measuring the incorporation signal, the controller 312 injects a low temperature wash into the solution sender 303, thereby washing out the non-reacted dNTP and the reaction products, i.e. hydrogen ions and diphosphates, and cools the chip using the cooler 300 simultaneously (S604).
(FIG. 7: Steps S605-S609)After finishing the washing process, the controller 312 selects the next dNTP (S605-S609), and then returns back to step S601 to repeat the same process. The incorporation signal measured by the ISFET 114 during the repeated process is converted into digital signals by an A/D converter included in the data processor 311 and is stored in a storage device included in the data processor 311 as measured data. The data processor 311 may identify the DNA structure according to the sequence acquired from the repeated process.
The output signal from the ISFET 114 acquired by the flowchart of
At time T0 in
The source line SLk and the data line DLAk, DLBk are connected to a k-th amplifier 2302-k in the reading circuit 309. This amplifier includes two typical current sources 1700 and 1704, two amplifiers 1701 and 1702, and an amplifier 1703 and a transistor 1705 for output. Operations of each amplifier when reading out the signal from the ISFET 114 will be described below.
The current sources 1700 and 1703 withdraw a constant current into the ground. The amplifiers 1701 and 1702 are amplifiers with voltage follower configuration and with gain of 1. The amplifiers 1701 and 1702 may be implemented by typical differential amplification circuits. These amplifiers generate, between DLAk and DLBk, a constant voltage VAB determined by the transistor 1705 and by a constant current Id flowing through the current source 1704. According to such configurations, the source-drain voltage Vds of the selected ISFET in the ISFET array is fixed approximately at VAB, and the drain current is fixed at the constant current Id determined by the current source 1700. When the ISFET 114 is working within a linear region, the drain current Id, the gate-source voltage Vgs, and the source-drain voltage Vds satisfy Equation 1 below. β is a constant unique to the ISFET 114 and Vth is the transistor threshold voltage of the ISFET 114.
Id=β{(Vgs−Vth)−½×Vds}×Vds (Equation 1)
When the threshold voltage of the ISFET 114 shifts by ΔVth due to ions in the solution, Equation 2 below is satisfied assuming that the drain current Id is constant and the source-drain voltage Vds is constant by the amplifier 2302-k.
Id=β{(Vgs′−(Vth+ΔVth))−½×Vds}×Vds (Equation 2)
Since Id is not 0, dividing Equation 1 by Equation 2 acquires Equation 3 below.
Vgs′−Vgs=ΔVth (Equation 3)
According to Equation 3, if the gate voltage (i.e. the voltage of the reference electrode 109) is fixed, the variation in the threshold voltage of the ISFET 114 is outputted as variation in the source voltage. Since Vds is constant, the variation in the source voltage equals to the variation in the drain voltage. Accordingly, ΔVth is outputted from the amplifier output terminal Ok. However, offset and background signal are overlapped with ΔVth. Thus as shown in
In the circuit diagram of
In accordance with the flowchart of
In addition, by subtracting the signal value immediately before heating by the heater 308 (i.e. the signal value including the component 1301 of drift and offset and the background component 1300) from the signal values after time T602, it is possible to readily acquire the incorporation signal waveform without these noises.
According to the above-mentioned configurations, the background estimation using a plurality of empty wells described in Patent Literature 2 is not necessary, thereby significantly reducing the processing load. In addition, the subtraction is performed using the measured value of the ISFET 114 itself that measures the incorporation signal 1302. Thus the subtraction is not influenced by characteristic variations of the ISFET 114.
Embodiment 1: VariationsIn the example described above, the cell is cooled using the wash and dNTP, and the cell is heated using the heater 308 on the chip to induce incorporation event. The method for controlling the temperature is not limited to above. For example, a cooling mechanism such as Peltier device may be contacted with the ISFET array chip 1002 to cool the chip. In addition, a typical heater may be contacted with the ISFET array chip 1002 to heat the chip. However, in the heating process for inducing incorporation event, it is preferable to rapidly change the temperature. This is because slow temperature change does not cause simultaneous incorporation events of copied DNAs on the bead 702, and thus the peak of the incorporation signal is not sharp.
It is preferable if the temperature of the reagent solution 108 after the heating process is near the optimum temperature at which DNA polymerase works most effectively. The optimum temperature significantly depends on the type of DNA polymerase. For example, if DNA polymerase is Klenow Fragment the optimum temperature is around 37 degrees centigrade, and if DNA polymerase is TaqDNA polymerase the optimum temperature is 70-75 degrees centigrade. If the temperature is too high, the enzyme may be denatured to be deactivated. Thus excessive heating should be avoided. In order to avoid such excessive heating: electric current may be caused to flow through the wire 900 for a predetermined period; or the temperature sensor 307 may be installed on the ISFET array chip 1002 and the heater 308 may be controlled while monitoring the temperature so that the temperature becomes around the optimum temperature.
The example above heats DNA polymerase up to the optimum temperature to induce incorporation event of DNA. However, incorporation event may be induced by controlling the temperature above the optimum temperature down to the optimum temperature.
The trigger inducing incorporation event is not limited to temperature. For example, if the light responsive nucleotide described in JP Patent Publication (Kokai) 2009-126789 A is used as the reagent solution 108, UV irradiation at wavelength of 366 nm may be used as the trigger for incorporation event. LEDs available on the market may be used as the UV light source of wavelength 366 nm. Alternatively, the reagent solution 108 may be separated into a buffer solution that does not induce incorporation event and a dNTP reagent. The cell may be filled with the buffer solution firstly and then the dNTP reagent may be injected. In this case, the injection of dNTP reagent works as trigger. In any cases, the functional unit that generates the trigger inducing incorporation event corresponds to “trigger generator”.
In
As shown in
As shown in
As discussed thus far, the biomolecule measuring device according to the embodiment 1 generates a trigger for the reagent solution 108 to react using the heater 308 or other alternative means, after the solution sender 303 starts transmitting the reagent solution 108 or more preferably after the solution sender 303 completes transmission of the reagent solution 108. Accordingly, it is possible to temporally separate the incorporation signal 1302 from the background as shown in
The biomolecule measuring device according to the embodiment 1 includes a circuit that fixes the drain current of ISFET 114 at Id and that fixes the source-drain voltage Vds at VAB. Accordingly, as shown in Equation 3, it is possible to extract only the threshold variation ΔVth of the ISFET 114 from the output terminal Ok.
The biomolecule measuring device according to the embodiment 1 is capable of subtracting the drift and offset component 1301 and the background component 1300 detected by each of the ISFET 114, by using the signals outputted from each of the ISFETs 114 only. Accordingly, it is possible to suppress computational loads for detecting the background. Further, the data value range is narrowed by suppressing the offset range. Thus it is possible to reduce conversion precision of A/D converter and amount of data.
Embodiment 2The embodiment 1 performs subtracting calculation in which the drift and offset component 1301 and the background 1300 are subtracted from the signal waveform detected by the ISFET 114, thereby extracting the incorporation signal 1302 only. An embodiment 2 of the present invention describes another configuration example for subtracting the drift and offset component 1301 and the background 1300.
In the embodiment 2, the floating gate 102 is connected to a voltage source (such as ground) via a transistor 1500. The voltage source fixes the voltage of a gate input 102 of the ISFET 114 and is not necessarily a ground. The transistor 1500 is controlled by a driving signal φ generated by the controller 312. The transistor 1500 turns ON/OFF the connection between the floating gate 102 and the voltage source. Other configurations are same as those of the embodiment 1.
These steps are same as steps S600-S601 in
The controller 312 applies a Hi signal as the driving signal φ for the transistor 1500. When the transistor 1500 is turned ON, the voltage of the floating gate 102 is fixed at ground voltage. Accordingly, the background 1300 and the drift and offset component 1301 are reset. After these noises are reset, the controller 312 turns OFF the transistor 1500. The signal waveform detected by the ISFET 114 in this step will be described in
These steps are same as steps S602-S609 in
As shown in
In
As discussed thus far, the biomolecule measuring device according to the embodiment 2 includes the transistor 1500 that turns ON/OFF the connection between the floating gate 102 and the voltage source. The biomolecule measuring device turns ON the transistor 1500 before measuring the incorporation signal 1302 to reset the noises. Accordingly, the process for subtracting the noise components is not necessary, thereby reducing the computational loads of the data processor 311. In addition, it is possible to decrease the dynamic range of A/D converter and amount of data.
The embodiment 2 outputs the incorporation event trigger to measure the incorporation signal 1302 after resetting the noises using the transistor 1500. However, even if the incorporation event trigger is not used, it is possible to cancel the drift and offset component 1301 using the transistor 1500. In this case, the temperature sensor 307, the heater 308, and the cooler 300 are not necessary, thereby simplifying the system configuration. In this case, the driving sequence of the biomolecule measuring device corresponds to the flowchart of
The embodiments 1-2 describe configuration examples where the drift and offset component 1301 and the background component 1300 are removed, thereby improving the signal quality of the ISFET 114. An embodiment 3 of the present invention describes a configuration example where the signal quality of the ISFET 114 is improved by other means.
The extra solution remover 315 is a device that removes reagent solutions outside the well 703. The extra solution remover 315 is controlled by the controller 312. The extra solution remover 315 may be implemented by pumps for sending a medium 1107 into the cell described in
In
These steps are same as steps S1600-S1602 in
The controller 312 drives the extra solution remover 315 to discharge the extra dNTP solution 1101 outside the well 703 from the outlet 1104, as shown in
These steps are same as steps S1603-S1610 in
The extra solution remover 315 separates each of the wells 703 during incorporation event of DNA. Thus it is possible to prevent the hydrogen ion 408 from spreading between the wells 703. In other words, it is possible to prevent cross talks between adjacent wells. In addition, the dNTP solution 1101 only exists in the well 703. Thus it is possible to prevent the generated hydrogen ion 408 from spreading to outside of the well 703 or from being vanished due to buffer effect of the solution outside of the well 703, thereby preventing the output signal of the ISFET 114 from being diminished. Accordingly, it is expectable to increase the crest value of the incorporation signal 1302 to improve the duration of signal.
If each of the wells 703 is separated from each other by removing the extra dNTP solution 1101, the connectivity between the reference electrode 109 and the dNTP solution 1101 in the well 703 may be degraded. In such cases, the reference electrode 109 may be installed in each of the wells 703 individually.
In order to readily remove the extra dNTP solution 1101, the substrate surface of the ISFET array chip 1002 may be coated with material that is water-repellent against the dNTP solution 1101. Accordingly, it is possible to reduce possibility with which the extra dNTP solution 1101 is not removed from the substrate surface. The water-repellency of the coat material would be effective enough as long as it promotes the extra dNTP solution 1101 to be removed. Specifically, fluorochemical coating agents available on the market, such as Teflon (registered trademark, DuPont) or CYTOP (registered trademark, Asahi Glass), may provide the water-repellency. Further, it is possible to increase the water-repellency by processing concavity and convexity on the surface.
Embodiment 3: VariationsAs discussed thus far, the biomolecule measuring device according to the embodiment 3 separates each of the wells 703 from each other to prevent the signal components from interfering between adjacent wells 703 due to cross talks. Thus it is possible to improve the signal quality of the ISFET 114.
The present invention is not limited to the embodiments, and various modified examples are included. The embodiments are described in detail to describe the present invention in an easily understood manner, and the embodiments are not necessarily limited to the embodiments that include all configurations described above. Part of the configuration of an embodiment can be replaced by the configuration of another embodiment. The configuration of an embodiment can be added to the configuration of another embodiment. Addition, deletion, and replacement of other configurations are also possible for part of the configurations of the embodiments.
For example, the embodiments 1-3 describe examples that measure reactions of sample DNAs fixed on the bead 702. As a modified example for fixing DNA, DNA may be fixed in the well 703 which surface is chemically modified. Accordingly, it is possible to reduce a possibility with which the bead 702 and the sample DNA are washed away when exchanging the solution.
The present invention is not limited to measuring devices that identify structures of DNA samples. The present invention may be applied to general measuring devices that detect ions generated by reactions between biomolecule samples and reagents. ISFET is described as a semiconductor sensor that detects ions. However, other sensors may be used as long as providing same functionalities.
REFERENCE SIGNS LIST
- 100 ion sensitive layer
- 101 protection layer
- 102 floating gate
- 103 gate electrode
- 104 gate oxide
- 105 drain
- 106 source
- 107 Si substrate
- 108 reagent solution
- 109, 1109 reference electrode
- 110 substrate contact
- 111, 112, 113, 703 well
- 114 ISFET
- 115 DNA
- 116 cell
- 300 cooler
- 301 reagent container
- 302, 313, 314, 316 reagent solution route
- 303 solution sender
- 304 ISFET array
- 305 selector circuit
- 307 temperature sensor
- 308, 1110 heater
- 309 reading circuit
- 310 waste solution
- 311 data processor
- 312 controller
- 315 extra solution remover
- 1002 ISFET array chip
- 1003, 1701, 1702, 2302 amplifier
- 1101 dNTP solution
- 1102 wash
- 1103 inlet
- 1104 outlet
- 1105 background measuring cell
- 1106 reading circuit
- 1107 medium
- 1108 structure
- 1111, 1112 wire
- 1200, 1201 selection transistor
- 1300 background component
- 1301 drift and offset component
- 1302 component derived from incorporation event
- 1303 signal reference level
- 1500 transistor
- 1700, 1703, 1704 current source
- 1705 transistor
- 2303 cell
- DLA, DLA1, DLAk, DLB, DLB1, DLBk data line
- O1, O2, Ok amplifier output terminal
- SL, SL1, SL2, SLk source line
Claims
1. A biomolecule measuring device comprising:
- a solution sender that transmits a reagent that undergoes a chemical reaction with a biomolecule sample to generate an ion;
- a semiconductor sensor that measures a concentration of the ion;
- a trigger generator that generates a physical environment that induces the chemical reaction;
- a controller that controls an operation of the solution sender and of the trigger generator; and
- a processor that identifies a configuration of the biomolecule sample according to a measured result by the semiconductor sensor,
- wherein the controller controls the solution sender and the trigger generator so that the trigger generator generates the physical environment after the solution sender starts transmitting the reagent onto the biomolecule sample disposed on the semiconductor sensor.
2. The biomolecule measuring device according to claim 1,
- wherein the controller controls the solution sender and the trigger generator so that the trigger generator generates the physical environment after the solution sender finishes transmitting the reagent,
- wherein the controller causes the solution sender and the trigger generator to repeat an operation of transmitting the reagent while exchanging a plurality of types of the reagent and an operation of generating the physical environment,
- and wherein the processor identifies a configuration of the biomolecule sample according to each of measured results acquired by the semiconductor sensor in the repeated operations.
3. The biomolecule measuring device according to claim 2,
- wherein the semiconductor sensor further comprises a transistor that has a drain terminal outputting the measured result as an electric signal,
- wherein the biomolecule measuring device further comprises a circuit that keeps a drain current of the transistor and a source-drain voltage of the transistor at constant values respectively,
- and wherein the processor performs a difference calculation subtracting, from the measured result after the trigger generator generates the physical environment, the measured result from when the solution sender finishes transmitting the reagent to when the trigger generator generates the physical environment, thereby removing a noise caused due to the reagent from the measured result.
4. The biomolecule measuring device according to claim 3,
- wherein the biomolecule measuring device comprises a plurality of the semiconductor sensors arranged in arrayed manner,
- and wherein the processor performs the difference calculation for each of the semiconductor sensors by separately using only the measured result of each of the semiconductor sensors respectively.
5. The biomolecule measuring device according to claim 3,
- wherein the biomolecule measuring device comprises two units of the semiconductor sensors arranged at a upstream side in a direction to which the solution sender transmits the reagent and at a downstream side in the direction respectively,
- wherein the circuit keeps a drain current and a source-drain voltage of the semiconductor sensor arranged at the downstream side at constant values respectively,
- and wherein the processor removes a noise due to the reagent from a measured result of each of the semiconductor sensors using a measured result of the semiconductor sensor arranged at the downstream side.
6. The biomolecule measuring device according to claim 2,
- the processor calculates a temporal differential value of a measured result of the semiconductor sensor,
- and wherein the controller controls the trigger generator so that the trigger generator generates the physical environment at a time point when the temporal differential value is at or below a predetermined threshold.
7. The biomolecule measuring device according to claim 1,
- wherein the trigger generator generates the physical environment by controlling temperature of the reagent or by irradiating an ultraviolet ray onto the reagent.
8. The biomolecule measuring device according to claim 1,
- wherein the solution sender transmits a reagent that causes the chemical reaction after transmitting a buffer solution that does not cause the chemical reaction.
9. The biomolecule measuring device according to claim 2,
- wherein the semiconductor sensor comprises a transistor that has a drain terminal outputting the measured result as an electric signal,
- wherein the biomolecule measuring device comprises: a voltage source that supplies a constant voltage to a gate electrode of the transistor; and a switching device that turns ON/OFF a connection between the voltage source and the gate electrode of the transistor,
- wherein the controller causes the trigger generator to generate the physical environment after turning ON the switching device to connect the voltage source with the gate electrode of the transistor,
- and wherein the processor identifies a configuration of the biomolecule sample without removing a noise due to the reagent from the measured result.
10. The biomolecule measuring device according to claim 2,
- wherein the biomolecule measuring device comprises a concave portion that houses the reagent,
- wherein the semiconductor sensor is connected to a bottom of the concave portion,
- and wherein the biomolecule measuring device further comprises a remover that removes an extra portion of the reagent that is present outside of the concave portion.
11. The biomolecule measuring device according to claim 9,
- wherein the biomolecule measuring device comprises a concave portion that houses the reagent,
- wherein the biomolecule measuring device further comprises a remover that removes an extra portion of the reagent that is present outside of the concave portion,
- and wherein the controller turns OFF the switching device to shut off between the voltage source and the gate electrode of the transistor after the remover removes an extra portion of the reagent, and then causes the trigger generator to generate the physical environment.
12. The biomolecule measuring device according to claim 10,
- wherein the biomolecule measuring device comprises a substrate on which the concave portion is formed,
- and wherein a surface of the substrate is coated with a material that is water-repellent against the reagent.
13. The biomolecule measuring device according to claim 2,
- wherein the biomolecule measuring device comprises a concave portion that houses the reagent,
- wherein the semiconductor sensor is connected to a bottom of the concave portion,
- and wherein the biomolecule measuring device further comprises a lid that seals the concave portion.
14. The biomolecule measuring device according to claim 13,
- wherein the trigger generator is attached to the lid,
- and wherein the trigger generator generates the physical environment so that the reagent housed in the concave portion induces the chemical reaction.
15. The biomolecule measuring device according to claim 1,
- wherein the semiconductor sensor is configured as an ion sensitive transistor that comprises:
- an ion sensitive layer which interface voltage changes due to the ion; and
- a transistor that outputs, as the measured result, an electric signal caused by a variation in the interface voltage.
Type: Application
Filed: Nov 18, 2013
Publication Date: Dec 17, 2015
Patent Grant number: 10451584
Inventors: Yoshimitsu YANAGAWA (Tokyo), Takahide YOKOI (Tokyo), Naoshi ITABASHI (Tokyo), Takayuki KAWAHARA (Tokyo), Sonoko MIGITAKA (Tokyo), Makiko YOSHIDA (Tokyo), Takamichi MURAMATSU (Tokyo)
Application Number: 14/759,596